JP7152538B2 - physiological measurement device - Google Patents

Description

[Incorporation by Reference to Priority Application]
119(e) from U.S. Provisional Application No. 62/188,430, filed July 2, 2015, entitled "Advanced Pulse Oximetry Sensor," which is herein incorporated by reference. ) claiming the benefit of priority under Any and all applications for which foreign or domestic priority claims are identified in an Application Data Sheet filed with this application are hereby incorporated by reference under 37 CFR 1.57.

FIELD OF THE DISCLOSURE The present disclosure relates to non-invasive light-based physiological monitoring sensors and, more particularly, to systems, devices and methods for increasing the accuracy of non-invasive measurements of oxygen saturation, among other physiological parameters.

Spectroscopy is a common technique for measuring the concentration of organic and some inorganic components of solutions. The theoretical basis of this technique is the Beer-Lambert law. Knowing the path length d _λ , the intensity of the incident light I _0,λ , and the extinction coefficient ε _i,λ at a particular wavelength λ, it is possible to determine the concentration c _i of the absorbing material in the solution as It states that it can be determined by the intensity of the transmitted light.

In generalized form, the Beer-Lambert law is expressed as:

where μ _α,λ is the bulk absorption coefficient and represents the probability of absorption per unit length. The minimum number of discrete wavelengths required to solve Eqs. 1 and 2 is the number of major absorbers present in the solution.

One practical application of this technique is pulse oximetry. It utilizes non-invasive sensors to measure oxygen saturation and pulse rate, among other physiological parameters. Pulse oximetry relies on sensors attached externally to the patient to detect, among other things, various physiological parameters such as patient blood components and/or analytes, including percent arterial oxygen saturation. output signals indicative of various physiological parameters. The sensor has an emitter that delivers light of one or more wavelengths to the tissue site and a detector that is responsive to the intensity of the light after absorption by pulsating arterial blood flowing through the tissue site. Based on this response, the processor derives oxygen saturation by determining the relative concentrations of oxygenated hemoglobin ( _HbO2 ) and deoxygenated hemoglobin (Hb). This can provide early detection of depletion of a potentially critical patient's oxygen supply.

A pulse oximetry system generally includes a patient monitor, a communication medium such as a cable, and/or one or more light emitters and detectors such as one or more light emitting diodes (LEDs) and photodetectors. Contains physiological sensors. The sensors are attached to tissue sites such as fingers, toes, earlobes, noses, hands, feet, or other sites with pulsatile blood flow through which light from one or more emitters can pass. A detector responds to the emitted light after attenuation or reflection by pulsatile blood flowing within the tissue site. The detector outputs detector signals to the monitor via a communication medium. The monitor processes the signals to provide numerical readouts of physiological parameters such as oxygen saturation (SpO2) and/or pulse rate. A pulse oximetry sensor is described in US Pat. No. 6,088,607, entitled Low Noise Optical Probe, and pulse oximetry signal processing is described in US Pat. Nos. 6,650,917, entitled Signal Processing Apparatus and Signal Processing Apparatus and Method, respectively. and U.S. Patent No. 6,699,194, and a pulse oximetry monitor is described in U.S. Patent No. 6,584,336 entitled Universal/Upgrading Pulse Oximeter, all of which are owned by Masimo Corporation of Irvine, Calif. and each of which is hereby incorporated by reference in its entirety.

There are many sources of measurement error introduced into pulse oximetry systems. Some sources of such errors include chemical and structural physiological differences between patients, as well as the electronic components of the pulse oximetry system, including the emitter and detector. Another source of measurement error is the effect of multiple scattering of photons. This is because the photons pass through the patient's tissue (arterial blood) and reach the photodetector of the sensor.

U.S. Patent No. 6,088,607 U.S. Patent No. 6,650,917 U.S. Patent No. 6,699,194 U.S. Patent No. 6,584,336

This disclosure describes, by non-limiting examples, oxygen, carboxyhemoglobin, methemoglobin, total hemoglobin, glucose, proteins, lipids, their percentages (e.g., saturation), pulse rate, perfusion index, oxygen content, total hemoglobin, To measure blood components, analytes, and/or substances such as the Oxygen Reserve Index™ (ORI™), or to measure many other physiologically relevant patient characteristics Embodiments of non-invasive methods, devices, and systems are described. These features can relate to, for example, pulse rate, hydration, trend information, and analysis.

In one embodiment, an optical physiological measurement system includes an emitter configured to emit light at one or more wavelengths. The system also receives the emitted light, diffuses the received light, and emits the diffused light to a larger tissue area than would be transmitted by the emitter directing the light to the tissue measurement site. a diffuser configured to. Tissue measurement sites can include, for example, fingers, wrists, and the like. The system further includes a concentrator configured to receive the diffused light after the diffused light has been attenuated by or reflected from the tissue measurement site. The concentrator is also configured to collect and focus the received light and emit the focused light to the detector. The detector is configured to detect the focused light and transmit a signal indicative of the detected light. The system also receives a transmitted signal indicative of the detected light and determines an analyte of interest, such as arterial oxygen saturation or other parameter, based on the amount of absorption at the tissue measurement site. including a processor configured to

In certain embodiments of the present disclosure, the diffuser is a glass, frosted glass, glass bead, opal glass, or microlens-based, band-limited, engineered A diffuser is included, and in some embodiments, the diffuser is further configured to define a surface area shape over which emitted diffuse light is dispersed over the surface of the tissue measurement site. Defined surface region shapes can include, in non-limiting examples, shapes that are substantially rectangular, square, circular, elliptical, or toric, among others.

According to some embodiments, an optical physiological measurement system includes an optical filter having a light absorbing surface facing a tissue measurement site. The optical filter also has an aperture configured to allow diffused light to be received by the concentrator after being attenuated by the tissue measurement site. In embodiments, the opening has a dimension, the dimension of the opening being similar to the shape of the defined surface area, thereby dispersing the emitted diffuse light to the surface of the tissue measurement site. In embodiments, the aperture has dimensions larger than the defined surface area shape, thereby dispersing the emitted diffuse light to the surface of the tissue measurement site. In other embodiments, the dimensions of the aperture in the optical filter are not the same as the diffuser aperture, but are larger than the detector package.

In other embodiments of the present disclosure, the concentrator comprises glass, frosted glass, glass beads, opal glass, or a compound parabolic concentrator. In some embodiments, the concentrator comprises a cylindrical structure having a truncated conical structure. The cropped portion is adjacent to the detector. The light concentrator is configured to receive the emitted light beam after reflection by the tissue measurement site and direct the reflected light to the detector.

According to certain embodiments of the present disclosure, the processor is configured to determine an average level of light detected by the detector. The average light level is used to determine a physiological parameter at the tissue measurement site.

According to another embodiment, a method is disclosed for determining a component or analyte in a patient's blood. The method comprises the steps of: emitting light of at least one wavelength from an emitter; using a diffuser to diffuse the emitted light and emitting the diffused light from the diffuser to a tissue measurement site; receiving the diffused light with a concentrator after it has been attenuated by the measurement site; focusing the received light with the concentrator; emitting the focused light from the concentrator to a detector; detecting the detected light with a detector; transmitting a signal from the detector in response to the detected light; and receiving, by a processor, the transmitted signal in response to the detected light. and processing, by a processor, the received signal responsive to the detected light to determine a physiological parameter.

In some embodiments, a method for determining a constituent or analyte in a patient's blood includes filtering a scattered portion of emitted diffuse light with a light absorption detector filter. According to one embodiment, the photoabsorption detector filter is substantially rectangular in shape, has outer dimensions in the range of about 1-5 cm wide and about 2-8 cm long, and emits It has an opening through which light can pass, the opening having dimensions in the range of about 0.25-3 cm in width and about 1-7 cm in length. In another embodiment, the light absorption detector filter is substantially square in shape, has outer dimensions in the range of about 0.25 to 10 cm ² , and has an opening through which emitted light can pass; The opening has a size in the range of about 0.1-8 cm ² . In yet another embodiment, the light absorption detector filter is substantially rectangular in shape and has outer dimensions of about 3 cm wide and about 6 cm long, with an aperture through which emitted light can pass. The opening has dimensions of about 1.5 cm in width and about 4 cm in length.

In yet another embodiment of the method for determining a constituent or analyte in a patient's blood, the steps of using a diffuser to diffuse the emitted light and emitting the diffused light from the diffuser to the tissue measurement site comprise: , a glass diffuser, a ground glass diffuser, a glass ball diffuser, an opaque glass diffuser, and an engineered diffuser. In some embodiments, the emitted diffuse light is emitted with a substantially constant intensity profile. And in some embodiments, the step of emitting diffused light from the diffuser to the tissue measurement site comprises emitting the emitted light such that the emitted diffused light defines a surface area shape distributed over the surface of the tissue measurement site. including the step of diffusing the

According to yet another embodiment, pulse oximetry is disclosed. Pulse oximetry includes an emitter configured to emit light at one or more wavelengths. The pulse oximetry also includes a diffuser configured to receive the emitted light, diffuse the received light, and emit the diffused light toward the tissue measurement site. Pulse oximetry also includes a detector configured to detect the emitted diffuse light after it has been attenuated by or reflected from the tissue measurement site and to transmit a signal indicative of the detected light. including. Pulse oximetry also receives the transmitted signal and measures the average absorbance of a blood component or analyte at a tissue measurement site over a measurement site area that is wider than can be performed with a point light source or point detector. A processor configured to process the received signal to determine. In some embodiments, the diffuser is further configured to define a surface area shape over which the emitted diffused light is dispersed to the surface of the tissue measurement site, and the detector further determines that the emitted diffused light is distributed over the surface of the tissue measurement site. It is configured to have detection regions corresponding to defined surface area shapes distributed over the surface of the site. According to some embodiments, the detector comprises an array of detectors configured to cover the detection area. In yet another embodiment, the processor is further configured to determine the average of the detected light.

For purposes of summarization, certain aspects, advantages and novel features of the disclosure have been described herein. It should be understood that all such advantages need not necessarily be achieved in accordance with any particular embodiment of the systems, devices and/or methods disclosed herein. . Accordingly, the presently disclosed subject matter provides one advantage, or group of advantages, as taught herein without necessarily achieving other advantages that may be taught or suggested herein. It can be embodied or executed in a manner that achieves or optimizes.

Throughout the drawings, reference numerals may be reused to indicate correspondence between referenced elements. The drawings are provided to illustrate embodiments of the disclosure described herein and not to limit their scope.

1 illustrates a conventional approach to two-dimensional pulse oximetry in which the emitter is configured to emit light rays as a point source; FIG. 2 illustrates the disclosed three-dimensional approach to pulse oximetry where the emitted light illuminates a substantially larger volume of tissue compared to the point source approach described with respect to FIG. 1. FIG. 1 is a schematic side view of a three-dimensional pulse oximetry sensor according to embodiments of the present disclosure; FIG. FIG. 3A is a plan view of a portion of a three-dimensional pulse oximetry sensor according to an embodiment of the present disclosure; 4B is a plan view of a portion of the three-dimensional pulse oximetry sensor illustrated in FIG. 4A with tissue measurement sites added to the operating position; FIG. 1 is a plan view of a three-dimensional pulse oximetry sensor according to embodiments of the present disclosure; FIG. 1 illustrates a conventional two-dimensional approach to reflective pulse oximetry in which the emitter is configured to emit light rays as a point source; FIG. 1 is a simplified schematic side view of a reflective three-dimensional pulse oximetry sensor according to embodiments of the present disclosure; FIG. 7B is a simplified schematic plan view of the three-dimensional reflective pulse oximetry sensor of FIG. 7A; FIG. 1 is a block diagram of an exemplary pulse oximetry system capable of non-invasively measuring one or more blood analytes in a monitored patient, according to embodiments of the present disclosure; FIG.

FIG. 1 schematically illustrates a conventional pulse oximetry sensor with a two-dimensional (2D) approach to pulse oximetry. As illustrated, emitter 104 is configured to emit light as a point light source, ie, a light source whose dimensions are negligible so that it can be considered a point. This approach is referred to herein as "two-dimensional" pulse oximetry because it applies a two-dimensional analytical model to the three-dimensional space of the patient's tissue measurement site 102 . A point light source is characterized by a defined, freely selectable, homogeneous light beam area. Light beams emitted from LED point sources often exhibit strong focusing. This can usually produce well-defined, evenly lit illumination spots, often with high intensity dynamics. Illustratively, when looking at the surface of tissue measurement site 102 (or “sample tissue”), which in this example is a finger, a small point-like surface area of tissue 204 is illuminated by a point light source. In some embodiments, the illuminated annular area of the point light source is in the range of 8-150 microns. Illustratively, the emitted light of the point source enters the tissue measurement site 102 as a point of light. As this light penetrates the tissue 102 in depth, it penetrates as lines or vectors, representing three-dimensional structures, ie, two-dimensional constructs within the patient's tissue 102 .

The use of point light sources is believed to reduce instability in optical path length, which can lead to more accurate oximetry measurements. In practice, however, photons do not travel straight paths, but instead light particles scatter and bounce back and forth among various irregular objects (eg, red blood cells, etc.) in the patient's blood. Thus, the photon path length varies, among other things, depending on the specific movement in or around tissue at the measurement site 102 . This phenomenon is called "multiple scattering". In one study, the effect of multiple scattering was examined by comparing the results of photon diffusion analysis with those obtained using a Beer-Lambert law-based analysis that ignores multiple scattering in determining the optical path length. rice field. Studies have shown that the difference in the average length of the paths traveled by red and infrared photons allows the oximetry calibration curve (based on measurements obtained from healthy subjects) to be used for pulse oximetry2. We found that it is sensitive not only to the total tissue attenuation coefficient in one wavelength band, but also to absorption by pulsating arterial blood.

FIG. 2 illustrates a method for performing three-dimensional (3D) pulse oximetry in which the emitted light illuminates a large volume of tissue at the measurement site 102 compared to the 2D point source approach described with respect to FIG. 1 schematically illustrates the disclosed system, device and method; In one embodiment, looking back at the surface of tissue measurement site 102, illuminated surface area 206 of measurement site 102 has dimensions within the range of approximately 0.25-3 cm in width and approximately 1-6 cm in length. , is substantially rectangular in shape. In another embodiment, illuminated surface area 206 of measurement site 102 is substantially rectangular in shape and has dimensions of about 1.5 cm in width and about 2 cm in length. In another embodiment, illuminated surface area 206 of measurement site 102 is substantially rectangular in shape and has dimensions of about 0.5 cm in width and about 1 cm in length. In another embodiment, illuminated surface area 206 of measurement site 102 is substantially rectangular in shape and has dimensions of about 1 cm in width and about 1.5 cm in length. In yet another embodiment, illuminated surface area 206 of measurement site 102 is substantially square in shape and has a size in the range of about 0.25-9 cm ² . In some embodiments, the illuminated surface area 206 of the measurement site 102 is approximately 0.5-2 cm wide and in the range of approximately 1-4 cm long. Of course, those skilled in the art will recognize that many other shapes and dimensions of illuminated surface area 206 may be used. Advantageously, by illuminating a tissue measurement site 102 having a surface area 206, the systems, devices, and methods disclosed herein generate a three-dimensional analytical model of the three-dimensional structure being measured, i.e., the patient. Apply to sample tissue 102 .

According to the Beer-Lambert law, the amount of light absorbed by a substance is proportional to the concentration of the light absorbing substance in the irradiated solution (ie arterial blood). Advantageously, by illuminating a larger volume of tissue 102, a larger sample size of light attenuated (or reflected) by tissue 102 is measured. A larger 3D sample, when passed through the patient's blood, provides a dataset that better represents the full interaction of the emitted light compared to the 2D point source approach described above with respect to FIG. By averaging the detected light as it is detected over a surface area substantially larger than a single point, the disclosed pulse oximetry systems, devices, and methods measure radiation absorbed by tissue. Provides more accurate measurements of light. This leads to a more accurate oxygen saturation measurement result.

FIG. 3 schematically illustrates a side view of a pulse oximetry 3D sensor 300 according to an embodiment of the present disclosure. In the illustrated embodiment, 3D sensor 300 illuminates tissue measurement site 102 and detects the emitted light after attenuation by tissue measurement site 102 . In other embodiments, the 3D sensor 300 can be positioned to detect light reflected by the tissue measurement site 102, eg, as described below with respect to FIGS. 7A and 7B. 3D sensor 300 includes emitter 302 , light diffuser 304 , light absorption detector filter 306 , light concentrator 308 , and detector 310 . In some optional embodiments, 3D sensor 300 further includes reflector 305 . Reflector 305 can be a metallic reflector or other type of reflector. Reflector 305 can be a coating, film, layer, or other type of reflector. Reflector 305 blocks emitted light from exiting the top of light diffuser 304 such that light from emitter 302 is directed into the tissue rather than escaping the sides or top of light diffuser 304. can act as a reflector for In addition, the reflector 305 can block ambient light from entering the diffuser 304 that can ultimately cause errors in the detected light. The reflector 305 also allows light from the detector 302 to escape from the light diffuser 304 when piped around the sensor securing mechanism to the detector 310 without passing through the patient's tissue 102. Block possible light piping.

Emitter 302 can act as a source of light that is transmitted toward tissue measurement site 102 . Emitter 302 may include one or more light sources such as LEDs, laser diodes, incandescent bulbs with appropriate frequency selective filters, combinations thereof, and the like. In one embodiment, emitter 302 includes a set of light sources capable of emitting visible and near-infrared light. In some embodiments, emitter 302 transmits red and infrared light at wavelengths of approximately 650 nm and approximately 940 nm, respectively. In some embodiments, emitter 302 includes a single light source.

Light diffuser 304 receives light emitted from emitter 302 and spreads the light over an area, such as area 206 illustrated in FIG. In some embodiments, the light diffuser 304 homogenizes the light beam input from the emitter 302, shapes the output intensity profile of the received light, and disperses the emitted light to the tissue measurement site 102 in a manner (e.g., , shape or pattern). Materials that may be used to implement the light diffuser 304 include, but are not limited to, white surface, glass, frosted glass, glass beads, polytetrafluoroethylene (also known as Teflon). glass), milk glass, and gray glass. Additionally, engineered diffusers can be used to implement diffuser 304 by providing customized light shaping in terms of intensity and dispersion. Such a diffuser may, for example, direct substantially constant illumination over a designated target area (eg, illuminated surface area 206) in an energy efficient manner. Examples of engineered diffusers can include plastic molded with specific shapes, patterns, or textures designed to diffuse the emitted light over the surface of the patient's tissue.

Advantageously, the diffuser 304 receives light emitted in the form of a point source and diffuses the light so as to conform it to the desired surface area of the plane defined by the surface of the tissue measurement site 102. can be made In an embodiment, the diffuser 304 is made of frosted glass that diffuses the emitted light with a Gaussian intensity profile. In another embodiment, diffuser 304 includes glass beads. In some embodiments, diffuser 304 is constructed to diffuse emitted light in a Lambertian pattern. A Lambertian pattern is one in which the radiant intensity is substantially constant over the area of dispersion. One such diffuser 304 is made from milk glass. Opaque glass is similar to frosted glass, but is coated on one side with an opaque coating to diffuse the light evenly. In one embodiment, the diffuser 304 directs the emitted light onto a planar surface (eg, the surface of the tissue measurement site 102) in a predefined shape (eg, rectangle, square, or circle), substantially It can be dispersed with a constant intensity profile and energy distribution. In some embodiments, this efficiency, the amount of light transmitted by diffuser 304, is greater than 70% of the light emitted by emitter 302. In some embodiments, this efficiency is greater than 90% of the emitted light. Other optical elements known in the art can be used for diffuser 304 .

In one embodiment, the diffuser 304 has a substantially rectangular shape with dimensions within the range of approximately 0.5-2 cm in width and approximately 1-4 cm in length. In another embodiment, the substantially rectangular shape of diffuser 304 has dimensions of about 0.5 cm in width and about 1 cm in length. In another embodiment, the substantially rectangular shape of diffuser 304 has dimensions of about 1 cm in width and about 1.5 cm in length. In yet another embodiment, diffuser 304 has a substantially square shape with a size in the range of approximately 0.25-10 cm ² .

The light absorption detector filter 306, also depicted in FIG. 4A in plan view, is a planar surface having an opening 402 through which emitted light can pass after being attenuated by the tissue measurement site 102. FIG. In the depicted embodiment, aperture 402 is rectangular in shape with dimensions substantially similar to illuminated surface area 206 . According to one embodiment, the light absorption detector filter is substantially rectangular in shape, has outer dimensions of 4 cm in width and 8 cm in length, and has an opening through which emitted light can pass. , the opening has dimensions of 2 cm in width and 5 cm in length. In another embodiment, the light absorption detector filter is substantially rectangular in shape and has outer dimensions in the range of 1-3 cm in width and 2-8 cm in length through which emitted light can pass. It has an opening, the opening having dimensions ranging from 0.25 to 2 cm in width and 1 to 4 cm in length. In yet another embodiment, the light absorption detector filter is substantially rectangular in shape, has outer dimensions of 3 cm wide by 6 cm long, and has an opening through which emitted light can pass. , the opening has dimensions of 1.5 cm in width and 4 cm in length.

The upper surface of light absorbing filter 306 (facing tissue measurement site 102 and emitter 302) is coated with a material that absorbs light, for example black pigment. Many other types of light absorbing materials are well known in the art and can be used with detector filter 306 . In operation, light emitted from the emitter 302 can be reflected from the tissue measurement site 102 (or other structure within the 3D sensor 300) toward a nearby portion of the 3D sensor 300. If these nearby portions of 3D sensor 300 have reflective surfaces, light may reflect back to tissue measurement site 102 and travel through this tissue to reach detector 310 . Such multiple scattering can result in the detection of photons with significantly longer path lengths than most of the detected light. This leads to path length variations that affect the accuracy of the pulse oximetry 3D sensor 300 measurements. Advantageously, light absorbing filter 306 reduces or reduces the amount of radiation reflected in this manner. This is because the light absorbing filter 306 stops the chain of scattering events by absorbing such reflected light. In some embodiments, the sensor-facing surfaces of other portions of the 3D sensor 300 are covered with a light-absorbing material to further reduce the effects of reflective multiple scattering.

Optical concentrator 308 is a structure for receiving the emitted light beam after attenuation by tissue measurement site 102 , collecting the dispersed light beam, focusing the collected light beam, and directing the focused light beam to detector 310 . be. In one embodiment, light concentrator 308 is made of ground glass or glass beads. In some embodiments, optical concentrator 308 includes a compound parabolic concentrator.

Detector 310 captures and measures light from tissue measurement site 102, as described above with respect to FIG. For example, detector 310 can capture and measure light transmitted from emitter 302 that is attenuated by tissue at measurement site 102 . Detector 310 can output a detection signal in response to captured or measured light. Detector 310 may be implemented using one or more photodiodes, phototransistors, or the like. Additionally, multiple detectors 310 can be arranged in an array having a spatial configuration corresponding to the illuminated surface area 208 to capture attenuated or reflected light from the tissue measurement site.

Referring to FIG. 4A, a plan view of a portion of 3D sensor 300 is provided. A light absorbing detector filter 306 is illustrated having a top surface coated with a light absorbing material. The light absorbing material can be a black opaque material or coating, or any other dark color or coating configured to absorb light. In addition, rectangular aperture 402 is positioned at light concentrator 308 (shown in phantom) so that light can pass through rectangular aperture 402 to light concentrator 308 and onto detector 310. ) and positioned relative to detector 310 . FIG. 4B illustrates a plan view of a portion of 3D sensor 300 as in FIG. 4A with tissue measurement site 102 added to the operating position. Accordingly, rectangular aperture 402 , optical concentrator 308 , and detector 310 are shown in phantom as underlying tissue measurement site 102 . Light concentrator 308 is illustrated in FIGS. 4A and 4B as having dimensions significantly larger than those of rectangular aperture 402 . In other embodiments, the dimensions of light concentrator 308, rectangular aperture 402, and illumination surface area 206 are substantially similar.

FIG. 5 illustrates a plan view of a 3D pulse oximetry sensor 500 according to an embodiment of the present disclosure. The 3D sensor 500 is configured to be worn on the patient's finger 102 . The 3D sensor 500 includes an adhesive substrate 502 having front flaps 504 and back flaps 506 extending outwardly from a central portion 508 of the 3D sensor 500 . A central portion 508 includes the components of the 3D pulse oximetry sensor 300 described with respect to FIGS. 3, 4A, and 4B. An emitter 302 and a light diffuser 304 are positioned on the front side of the adhesive substrate 502 . A light absorption detector filter 308, a light focuser 308, and a detector 310 are positioned on the back side of the adhesive substrate 502 so that, in use, the front portion of the adhesive substrate is folded over the tip of the patient's finger 102. A rectangular opening 402 in which the patient's finger becomes the tissue measurement site 102 so that the emitter 302 and light diffuser 304 align with the measurement site 102, filter 306, light concentrator 308, and detector 310 when superimposed on the placed above the Once alignment is established, the front flap 504 and back flap 506 can be wrapped around the finger measurement site 102 such that the adhesive substrate 502 provides secure contact between the patient's skin and the 3D sensor 500. can. FIG. 5 also shows an example sensor connector cable 510 used to connect the 3D sensor 500 to the monitor 809, as described with respect to FIG.

FIG. 6 is a simplified schematic illustration of a conventional 2D approach to reflective pulse oximetry in which the emitter is configured to emit light rays as point sources. Reflective pulse oximetry is a method in which the emitter and detector are placed on the same side of the tissue measurement site 102 . Light is emitted to the tissue measurement site 102 and attenuated. The emitted light passes through tissue 102 and then reflects to the same side of tissue measurement site 102 as the emitter. As illustrated in FIG. 6, the depicted reflective 2D pulse oximetry sensor 600 includes an emitter 602 , a shader 606 and a detector 610 . The light block 606 is necessary because the emitter 602 and the detector 610 are located on the same side of the tissue measurement site 102 . Thus, light block 606 blocks incident radiation that did not enter tissue measurement site 102 from reaching detector 610 . The depicted 2D pulse oximetry sensor 600 is configured to emit light as a point source. A simplified illustration of an optical path 620 of emitted light from emitter 602, through tissue measurement site 102, and to detector 610 is provided, as depicted in FIG. In particular, the light of a point light source is emitted and the light of the point light source is detected. As discussed above with respect to FIG. 1, the use of point sources can result in substantial measurement errors due to path length instabilities resulting from multiple scattering phenomena. The sample space provided by the 2D point light source is not long enough to account for path length instability, which distorts the measurement results.

7A and 7B are simplified schematic side and top views, respectively, of a 3D reflective pulse oximetry sensor 700 according to an embodiment of the present disclosure. In the illustrated embodiment, 3D sensor 700 illuminates tissue measurement site 102 and detects radiation reflected by measurement site 102 . Because emitter 702 and detector 710 are positioned on the same side of tissue measurement site 102, 3D sensor 700 can be positioned on a portion of the patient's body that has a relatively flat surface, such as the wrist. The 3D sensor 700 includes an emitter 702 , a light diffuser 704 , a shader 706 , a light concentrator 708 and a detector 710 .

As previously described, emitter 702 can act as a light source for light transmitted toward tissue measurement site 102 . Emitter 702 may include one or more light sources of light. Sources of such light can include LEDs, laser diodes, incandescent bulbs with appropriate frequency selective filters, combinations thereof, and the like. In one embodiment, emitter 702 includes a set of light sources capable of emitting visible and near-infrared light. In some embodiments, emitter 702 transmits red and infrared light at wavelengths of about 650 nm and about 940 nm, respectively. In some embodiments, the emitter 702 comprises a single beam light source.

Light diffuser 704 receives light rays emitted from emitter 302 and homogenizes the light rays over a wide, donut-shaped area, such as the area outlined by light diffuser 704, as depicted in FIG. 7B. Diffuse. Advantageously, the diffuser 704 can receive light emitted in the form of a 2D point source (or any other form) and direct the desired light on the plane defined by the surface of the tissue measurement site 102. This light can be diffused to match the surface area. In one embodiment, diffuser 704 is made of ground glass or glass beads. Those skilled in the art will appreciate that many other materials can be used to make the light diffuser 704 .

Shade 706 includes an annular ring with cover portion 707 sized and shaped to form a light separation chamber for light concentrator 708 and detector 710 (for illustrative purposes, shade cover 707 is not illustrated in FIG. 7B). Light shield 706 and cover 707 can be made of any material that optically isolates light concentrator 708 and detector 710 . The light isolation chamber formed by light shield 706 and cover 708 ensures that the only light detected by detector 710 is light reflected from the tissue measurement site.

The optical concentrator 708 is a cylindrical structure with a truncated conical structure, the truncated portion being adjacent to the detector 710 . Light concentrator 708 is configured to receive the emitted light beam after being reflected by tissue measurement site 102 and direct the reflected light to detector 710 . In an embodiment, light concentrator 708 is made from ground glass or glass beads. In some embodiments, optical concentrator 708 includes a compound parabolic concentrator.

Detector 710 captures and measures light from tissue measurement site 102 as previously described. For example, detector 710 can capture and measure light transmitted from emitter 702 that is reflected from tissue at measurement site 102 . Detector 710 can output a detector signal in response to captured or measured light. Detector 710 may be implemented using one or more photodiodes, phototransistors, or the like. Additionally, a plurality of detectors 710 are arranged in an array having a spatial configuration corresponding to the illuminated surface area depicted in FIG. obtain.

Advantageously, light path 720 illustrated in FIG. 7A depicts a substantial sample of reflected light entering the light isolation chamber formed by light blocker 706 and cover 707. In FIG. As discussed previously, in order to derive a more accurate measurement of the emitted light absorbed by tissue, a large amount of reflected light (compared to the reflected light collected using the 2D point source approach) A sample provides an opportunity for averaging the detected light. This leads to a more accurate oxygen saturation measurement result.

Referring now to FIG. 7B, a plan view of 3D sensor 700 is illustrated with both emitter 702 and shader cover 707 removed for ease of illustration. The outer ring exemplifies the installation area of the light diffuser 704 . When light is emitted from emitter 702 (not shown in FIG. 7B), the light is homogenously diffused and directed toward tissue measurement site 102 . A light block 706 forms the annular wall of the light isolation chamber to prevent incident light from being sensed by the detector 710 . The light block cover 707 prevents incident light from entering the light isolation chamber from above. Light concentrator 710 collects reflected light from tissue measurement site 102 and directs the reflected light upward toward detector 710 at the center of 3D sensor 700 .

FIG. 8 shows an example of an optical physiological measurement system 800, which may also be referred to as a pulse oximetry system 800 herein. In some embodiments, the pulse oximetry system 800 measures oxygen, carboxyhemoglobin, methemoglobin, total hemoglobin, glucose, proteins, lipids, their percentages (e.g., saturation), pulse rate, perfusion index, oxygen content. It non-invasively measures blood analytes such as amount, total hemoglobin, Oxygen Reserve Index™ (ORI™), or many other physiologically relevant patient characteristics. These features may relate to, for example, pulse rate, hydration, trend information, and analysis. The system 800 can also measure additional blood analytes and/or other physiological parameters useful in determining a patient's health status or trend.

Pulse oximetry system 800 can measure analyte concentration, at least in part, by detecting light attenuated by tissue at measurement site 102 . The measurement site 102 can be anywhere on the patient's body, such as fingers, feet, earlobes, wrists, forehead, and the like.

The pulse oximetry system 800 can include a sensor 801 (or multiple sensors) coupled to a processing device or physiological monitor 809 . In one embodiment, sensor 801 and monitor 809 are integrated together into a single unit. In another embodiment, sensor 801 and monitor 809 are remote from each other and communicate with each other in any suitable manner, such as via wired or wireless connections. Sensor 801 and monitor 809 may be detachable from each other for user or caregiver convenience, for ease of storage, for hygiene concerns, and the like.

In the depicted embodiment shown in FIG. 8, sensor 801 includes emitter 804 , detector 806 and front end interface 808 . Emitter 804 can act as a source of light that is transmitted to measurement site 102 . Emitter 804 can include one or more light sources such as light emitting diodes (LEDs), laser diodes, incandescent bulbs with appropriate frequency selective filters, combinations thereof, and the like. In one embodiment, emitter 804 includes a set of light sources capable of emitting visible and near-infrared light.

Pulse oximetry system 800 also includes driver 811 that drives emitter 804 . Driver 811 can be a circuit or the like controlled by monitor 809 . For example, driver 811 can provide a pulse of current to emitter 804 . In one embodiment, driver 811 drives emitters 804 in a stepped fashion, such as an alternating fashion. Driver 811 can drive emitter 804 with a series of pulses for some wavelengths that can penetrate tissue relatively well, and other wavelengths that tend to be heavily absorbed by tissue. A wide variety of other drive powers and drive methods may be used in various embodiments. Driver 811 can be synchronized with the rest of sensor 801 to minimize or reduce jitter in the timing of pulses of light emitted from emitter 804 . In some embodiments, driver 811 can drive emitter 804 to emit light in a pattern that varies less than about 10 ppm.

Detector 806 captures and measures light from tissue measurement site 102 . For example, detector 806 can capture and measure light transmitted from emitter 804 that is attenuated or reflected in tissue at measurement site 102 . Detector 806 can output a detector signal 107 in response to the captured and measured light. Detector 806 may be implemented using one or more photodiodes, phototransistors, or the like. In some embodiments, the detector 806 is mounted within a detector package to capture and measure light from the tissue measurement site 102 of the patient. A detector package can include a photodiode chip attached to a lead and surrounded by an encapsulant. In some embodiments, the size of the detector package is about 2 square centimeters. In other embodiments, the dimensions of the detector package are about 1.5 centimeters wide and about 2 centimeters long.

Front-end interface 808 provides an interface for adapting the output of detector 806, which corresponds to a desired physiological parameter. For example, front-end interface 808 can adapt signal 807 received from detector 806 into a form that can be processed by monitor 809 , eg, by signal processor 810 in monitor 809 . The front end interface 808 can have components incorporated in the sensor 801, monitor 809, connecting cables (if used), combinations thereof, and the like. The location of front end interface 808 may be selected based on a variety of factors, including space desired for components, noise reduction or noise limiting desired, heat reduction or limiting desired, and the like.

Front end interface 808 may be coupled to detector 806 and signal processor 810 using a bus, wire, electrical or optical cable, flex circuit, or some other form of signal connection. Front end interface 808 may also be at least partially integrated with various components such as detector 806 . For example, front end interface 808 may include one or more integrated circuits on the same circuit board as detector 806 . Other configurations can also be used.

As illustrated in FIG. 8, monitor 909 can include signal processor 810 and a user interface such as display 812 . Monitor 809 may also include optional outputs such as storage device 814 and network interface 816 alone or in combination with display 812 . In one embodiment, signal processor 810 includes processing logic to determine a desired analyte measurement result based on the signal received from detector 806 . Signal processor 810 may be implemented using one or more microprocessors or sub-processors (e.g., cores), digital signal processors, application specific integrated circuits (ASICs), field programmable gate arrays (FPGAs), combinations thereof, or the like. can be implemented.

Processor signal 810 can provide various signals that control the operation of sensor 801 . For example, signal processor 810 can provide emitter control signals to driver 811 . This control signal can be useful for synchronizing, minimizing, or reducing jitter in the timing of pulses emitted from emitter 804 . Thus, this control signal can be useful to force the light pulses emitted from emitter 804 to follow precise timing and consistent patterns. For example, if a transimpedance-based front-end interface 808 is used, the control signal from the signal processor 810 should provide synchronization with the analog-to-digital converter (ADC) to avoid aliasing, crosstalk, etc. can be done. As further illustrated, optional memory 813 may be included in front end interface 808 and/or signal processor 810 . This memory 813 can serve as a buffer or storage location for the front end interface 808 and/or the signal processor 810, among other uses.

User interface 812 can provide output, for example, on a display, for presentation to a user of pulse oximetry system 800 . User interface 812 may be implemented as a touch screen display, liquid crystal display (LCD), organic LED display, or the like. In alternative embodiments, pulse oximetry system 800 may be provided without user interface 812 and simply provide output signals to a separate display or system.

Storage device 814 and network interface 816 represent other optional output connections that may be included in monitor 809 . Storage device 814 may include any computer-readable medium such as memory devices, hard disk storage, EEPROM, flash drives, and the like. Various software and/or firmware applications that may be executed by signal processor 810 or another processor in monitor 809 may be stored in storage device 814 . The network interface 816 includes serial bus ports (RS-232/RS-485), universal serial bus (USB) ports, Ethernet ports, wireless interfaces (e.g. WiFi like any 802.1x interface including internal wireless cards), Or, it can be any other suitable communication device that allows monitor 809 to communicate and share data with other devices. The monitor 809 may also include a microprocessor, graphics processor, or controller to output a user interface 812, control data communications, calculate data trends, or perform other operations. It may include various other components not shown, such as.

Although not shown in the depicted embodiment, the pulse oximetry system 800 can include various other components or can be configured in different ways. For example, sensor 801 can have both emitter 804 and detector 806 on the same side of tissue measurement site 102 and can use reflectance to measure the analyte.

Although the foregoing disclosure has been described with respect to several preferred embodiments, many other variations from those described herein will become apparent to those skilled in the art.

In particular, conditional statements used herein, such as "can," "may," "can," "for example," etc., are not specifically recited otherwise, or , unless otherwise understood in context when used, generally includes some features, elements, and/or states, while some embodiments include It is intended to convey that no Accordingly, such conditional statements state that the features, elements and/or states are in any manner required for one or more embodiments or that these features, elements and/or or whether a state should be included or executed in any particular embodiment, one or more of which determines, with or without input or prompting by the author It is not generally intended to imply necessarily including logic for Terms such as "comprising," "including," "having," etc. are synonymous and are used inclusively in an open-ended manner and do not exclude additional elements, features, acts, operations, and the like. Also, the term "or", e.g., when used to connect a list of elements, is such that the term "or" means one, some, or all of the elements in the list. used in an inclusive (and not exclusive) sense. Further, the term "each" as used herein, in addition to having its ordinary meaning, can refer to any subset of the set of elements to which the term "each" applies.

While the foregoing detailed description illustrates, describes, and points out novel features as applying to various embodiments, various omissions and substitutions in form and detail of the illustrated system, device, or algorithm have been made. , and modifications may be made without departing from the spirit of this disclosure. It will be appreciated that some features may be used or implemented in isolation from others, so some embodiments of the disclosure described herein may not necessarily represent the features and advantages recited herein. All may be embodied as non-provided forms.

The term "and/or" herein means that the disclosure includes only A, only B, both A and B, or alternatively A or B, but both A and B. or has the broadest and least exclusive meaning of requiring one of A or one of B. As used herein, "at least one of A, B," and "C" shall mean logical A or B or C, using the non-exclusive logical or. should be interpreted as

The apparatus and methods described herein can be implemented by one or more computer programs executed by one or more processors. A computer program comprises processor-executable instructions stored on a non-transitory, tangible computer-readable medium. Computer programs may also include stored data. Non-limiting examples of non-transitory tangible computer-readable media are non-volatile memory, magnetic storage, and optical storage. While the foregoing disclosure has been described with respect to several preferred embodiments, other embodiments will become apparent to those skilled in the art from the present disclosure. Additionally, other combinations, omissions, substitutions, and modifications will become apparent to those skilled in the art in view of the disclosure herein. Accordingly, the invention is not intended to be limited by the description of the preferred embodiments, but should be defined by reference to the appended claims.

In addition, all publications, patents and patent applications mentioned in this specification are herein specifically referred to as if each individual publication, patent or patent application was incorporated by reference. and incorporated by reference to the same extent as individually indicated.

[Section 1]
An optical physiological measurement system comprising:
an emitter that emits light of a certain wavelength;
a diffuser that receives and diffuses the light and emits diffuse light, wherein the emitted diffuse light is directed to a tissue measurement site of a patient;
a detector configured to detect the emitted light after attenuation by tissue of the patient, the detector further configured to transmit a signal in response to the detected light; optical physiological measurement system.
[Section 2]
2. The method of paragraph 1, further comprising a concentrator that receives the diffused light after attenuation by tissue of the patient, focuses the received diffused light, and emits the focused light toward the detector. Optical physiological measurement system.
[Section 3]
3. The optical physiological measurement system of paragraphs 1 or 2, further comprising a processor configured to receive the transmitted signal and determine a physiological parameter responsive to the detected light. .
[Section 4]
4. The optical physiological measurement system according to clause 3, wherein the physiological parameter is arterial blood oxygen saturation.
[Section 5]
5. The diffuser of any one of paragraphs 1-4, wherein the diffuser comprises at least one of a glass diffuser, a ground glass diffuser, a glass ball diffuser, an opalescent glass diffuser, and an engineered diffuser. Optical physiological measurement system.
[Section 6]
6. An optical physiological measurement system according to any one of the preceding clauses, wherein the diffuser emits the diffused light with a substantially constant intensity profile.
[Section 7]
7. The optical physiological measurement system of any one of the preceding paragraphs, wherein the diffuser defines a surface area shape over which the emitted diffuse light is distributed to the surface of the tissue measurement site.
[Section 8]
A detector filter further comprising a detector filter having a light absorbing surface facing the tissue measurement site and an aperture, the aperture having a dimension, the dimension of the aperture being such that the emitted diffused light passes through the tissue. 8. The optical physiological measurement system of clause 7, substantially similar to the defined surface area shape distributed over the surface of the measurement site.
[Section 9]
8. The optical physiological measurement system of clause 7, wherein the surface area shape is rectangular.
[Section 10]
10. The optical physiological measurement system of clause 9, wherein the rectangular surface area shape has dimensions within the range of about 0.25 cm to 3 cm in width and about 1 cm to 6 cm in length.
[Section 11]
10. The optical physiological measurement system of clause 9, wherein the rectangular surface area shape has dimensions within the range of about 0.1 cm to 2 cm in width and about 0.5 cm to 5 cm in length.
[Section 12]
10. The optical physiological measurement system of clause 9, wherein the rectangular surface area shape has dimensions of about 1 centimeter in width and about 1.5 centimeters in length.
[Section 13]
8. The optical physiological measurement system of clause 7, wherein the surface area shape is square.
[Section 14]
14. The optical physiological measurement system of clause 13, wherein the square surface area shape has a size within the range of about 0.25 cm2 to 10 cm2.
[Section 15]
further comprising a detector filter comprising a light absorbing surface facing said tissue measurement site and an aperture, said aperture having a dimension, said dimension of said aperture substantially the dimension of said rectangular shape. 10. An optical physiological measurement system according to Clause 9, which is similar to.
[Section 16]
16. The optical physiological measurement of any one of clauses 1-15, wherein the concentrator comprises at least one of glass, frosted glass, glass ball, milk glass, and compound parabolic concentrator. system.
[Section 17]
Further comprising a detector filter comprising a light absorbing surface facing the tissue measurement site, and an aperture, wherein the diffused light is attenuated by or away from the tissue measurement site. 17. An optical physiological measurement system according to any one of the preceding clauses, arranged to allow light to be received by said concentrator after being reflected.
[Section 18]
A method for determining a component or analyte in a patient's blood, comprising:
emitting light of a wavelength from an emitter;
using a diffuser to diffuse the emitted light and emit diffused light from the diffuser to the tissue measurement site, the diffuser causing the emitter to emit light directly to the tissue measurement site. spreading the light over an area of the tissue measurement site that is larger than it would be illuminated;
detecting the emitted focused light with a detector;
method including.
[Section 19]
After the diffused light has been attenuated by the tissue measurement site or reflected from the tissue measurement site, the emitted diffused light is received by a concentrator, the received light is focused by the concentrator, and the 19. The method of clause 18, further comprising emitting focused light from the concentrator to a detector.
[Section 20]
transmitting a signal from the detector in response to the detected light;
receiving by a processor the transmitted signal responsive to the detected light;
processing by the processor the received signal responsive to the detected light to determine a physiological parameter;
20. The method of paragraph 18 or 19, further comprising:
[Section 21]
21. The method of any one of clauses 18-20, further comprising filtering the scattered portion of the emitted diffuse light with a light absorption detector filter.
[Section 22]
The steps of using a diffuser to diffuse the emitted light and emitting the diffused light from the diffuser to the tissue measurement site may include glass diffusers, glass bead diffusers, opaque glass diffusers, and engineered diffusers. 22. The method of any one of paragraphs 18-21, performed by at least one of:
[Section 23]
diffusing the emitted light with a diffuser and emitting the diffused light from the diffuser to the tissue measurement site further comprises diffusing the emitted light with a substantially constant intensity profile; 23. The method of any one of paragraphs 18-22.
[Section 24]
The step of using a diffuser to diffuse the emitted light and emitting the diffused light from the diffuser to the tissue measurement site further comprises a surface area over which the emitted diffused light is dispersed over the surface of the tissue measurement site. Clause 24. The method of any one of clauses 18-23, comprising diffusing the emitted light so as to define a shape.
[Section 25]
The step of focusing received light by a concentrator and emitting said focused light from said concentrator to a detector comprises: a glass concentrator; a glass ball concentrator; 25. The method of any one of paragraphs 18-24, performed by at least one of
[Section 26]
A pulse oximetry sensor,
an emitter configured to emit light at a wavelength;
a diffuser configured to receive the emitted light, diffuse the received light, and emit diffuse light, wherein the emitted diffuse light is directed toward a tissue measurement site; and the radiation. a detector configured to detect diffused light, the diffused light being attenuated by the tissue measurement site, the detector further outputting a signal in response to the detected light a detector configured to
A pulse oximetry sensor, comprising:
[Section 27]
27. The pulse oximetry of clause 26, further comprising a concentrator that focuses the emitted light after the emitted light is attenuated by the tissue measurement site and directs the focused light to the detector. sensor.
[Section 28]
The detector is further configured to output the signal responsive to the detected light to a processor configured to receive the signal responsive to the detected light and determine a physiological parameter. 28. The pulse oximetry sensor of clause 26 or clause 27, wherein the pulse oximetry sensor is
[Section 29]
Clause 29. The pulse oxygen of any one of clauses 26-28, wherein the diffuser is further configured to define a surface area shape over which the emitted diffuse light is dispersed to a surface of the tissue measurement site. metric sensor.
[Section 30]
30. The detector of clause 29, wherein the detector is further configured to have a detection area corresponding to the defined surface area shape over which the emitted diffuse light is distributed to the surface of the tissue measurement site. Pulse oximetry sensor.
[Section 31]
Clause 31. The pulse oximetry sensor of clause 30, wherein the detector further comprises an array of detectors configured to cover the detection area.
[Section 32]
A pulse oximetry sensor,
an emitter configured to emit light at a wavelength;
a concentrator for focusing the emitted light after the emitted light has been attenuated by a tissue measurement site;
a detector configured to detect the emitted light, wherein the emitted light is attenuated by or reflected from the tissue measurement site; is further configured to output a signal in response to said detected light;
A pulse oximetry sensor comprising:
[Section 33]
The detector is further configured to send an output signal responsive to the detected light to a processor configured to receive the signal responsive to the detected light and determine a physiological parameter. 33. The pulse oximetry sensor of clause 32, wherein the pulse oximetry sensor is
[Section 34]
Clause 32. The pulse oximetry sensor of Clauses 32 or 33, wherein the concentrator is further configured to define a surface area shape over which the emitted diffuse light is received from a surface of the tissue measurement site.
[Section 35]
Clause 35. The concentrator of clause 34, wherein the concentrator is further configured to have a detection area corresponding to the defined surface area shape over which the emitted diffuse light is distributed to the surface of the tissue measurement site. Pulse oximetry sensor.
[Section 36]
Clause 36. The pulse oximetry sensor of clause 35, wherein the detector further comprises an array of detectors configured to cover the detection area.

102 Tissue measurement site
104 Emitter
206 surface area
300 pulse oximetry sensor
302 Emitter
304 Diffuser
305 Reflector
306 Photo Absorption Detector Filter
308 Optical Concentrator
310 detector
402 opening
502 Adhesive Substrate
504 front flap
508 central part
506 back flap
510 sensor connector cable
600 pulse oximetry sensor
602 Emitter
606 light block
610 detector
620 optical paths
700 Reflective Pulse Oximetry Sensor
702 Emitter
704 Light Diffuser
706 Shading part
707 Light shield cover
708 Light Concentrator
710 detector
720 light paths
800 pulse oximetry system
801 sensor
804 Emitter
806 detector
807 Signal
808 front-end interface
809 monitor
810 signal processor
811 drivers
812 User Interface
813 memory
814 storage
816 network interface

Claims (25)

A physiological measurement device comprising:
one or more emitters configured to emit light in an initial light pattern;
A light transmissive material configured to be positioned between the one or more emitters and a tissue measurement site when the physiological measurement device is in use, the light transmissive material configured to be positioned between the one or more to form an output light pattern different from the initial light pattern such that the emitted light is directed at the surface of the tissue measurement site. a light transmissive material comprising;
A plurality of detectors configured to detect at least a portion of the light after it has passed through tissue, the plurality of detectors configured to output at least one signal in response to the detected light. vessel and
a light shield forming a light isolation chamber separating the plurality of detectors from the one or more emitters during use of the physiological measurement device at the tissue measurement site, the one or more emitters a light block configured to block at least some of the light emitted from reaching the plurality of detectors without first reaching tissue;
The plurality of surfaces comprising a dark coating, wherein openings defined in the dark coating are configured to allow at least a portion of light reflected from the tissue to pass through the surface. a surface positioned between the detector of and the tissue;
A processor for receiving and processing one or more signals responsive to at least one output signal, the processor being configured to determine a physiological parameter of a user responsive to said one or more signals. a processor;
A physiological measurement device comprising: wherein the light block comprises an at least partially circular shape, the one or more emitters are positioned outside the light block, and the plurality of detectors are positioned inside the light block. The physiological measurement device of claim 1, characterized by: 2. The physiological measurement device of claim 1, wherein said light transmissive material comprises glass. 2. The physiological measurement device of claim 1, wherein said light transmissive material comprises plastic. 2. The physiological sensor according to claim 1, wherein the plurality of detectors are arranged in an array having a spatial configuration corresponding to the shape of a portion of the tissue measurement site partitioned by the light shielding section. measuring device. 2. The physiological measurement device of claim 1, wherein said dark coating comprises black pigment. 3. The physiological measurement device of claim 1, wherein the physiological measurement device is configured to wirelessly transmit physiological parameter data to a separate device. 3. The physiological measurement device of Claim 1, further comprising a touch screen display configured to present information related to the determined physiological parameter. 2. The physiological measurement device of claim 1, wherein said output light pattern comprises a width and a length, said width being different than said length. 3. The physiological measurement device of Claim 1, wherein said output light pattern comprises an elliptical shape. A physiological measuring device according to claim 1, characterized in that said physiological parameter is oxygen saturation. Physiological measuring device according to claim 1, characterized in that the physiological parameter is pulse rate. 3. The physiological measurement device of claim 1, wherein said opening defined in said dark coating includes a width and a length, said length being greater than said width. A physiological measurement device comprising:
one or more light sources configured to emit light at one or more wavelengths in an initial light pattern, the one or more light sources proximate a user's wrist;
A light transmissive material configured to be positioned between the one or more light sources and a tissue measurement site when the physiological measurement device is in use, the light transmissive material configured to be positioned between the one or more to form an output light pattern different from the initial light pattern such that the emitted light impinges on the surface of the tissue measurement site. a light transmissive material, comprising
a plurality of detectors configured to detect at least a portion of the light after it has passed through tissue, and configured to output at least one signal in response to the detected light; or multiple detectors, wherein the multiple light sources and multiple detectors are arranged in a reflectometric configuration;
a light shield forming a light isolation chamber separating the plurality of detectors from the one or more light sources during use of the physiological measurement device at the tissue measurement site, the one or more light sources a light block configured to block at least some of the light emitted from reaching the plurality of detectors without first reaching tissue;
The plurality of surfaces comprising a dark coating, wherein openings defined in the dark coating are configured to allow at least a portion of light reflected from the tissue to pass through the surface. a surface positioned between the detector of and the tissue;
A processor for receiving and processing one or more signals responsive to at least one output signal, the processor being configured to determine a physiological parameter of a user responsive to said one or more signals. a processor;
a touch screen display configured to present information responsive to the determined physiological parameter;
A physiological measurement device comprising:
A physiological measurement device configured to wirelessly transmit physiological parameter data to a separate device. wherein the light block comprises an at least partially circular shape, the one or more light sources are positioned outside the light block, and the plurality of detectors are positioned inside the light block. 15. The physiological measurement device of claim 14, characterized by: 15. The physiological measurement device of Claim 14, wherein the light transmissive material comprises at least one of glass and plastic. 15. The physiological measurement device of claim 14, wherein said output light pattern comprises a width and a length, said width being different than said length. 15. A physiological measuring device according to claim 14, characterized in that said physiological parameter is oxygen saturation. 15. A physiological measuring device according to claim 14, characterized in that said physiological parameter is pulse rate. 15. The physiological measurement device of claim 14, wherein said opening defined in said dark coating comprises a width and a length, said length being greater than said width. 15. The physiological sensor according to claim 14, wherein the plurality of detectors are arranged in an array having a spatial configuration corresponding to the shape of a portion of the tissue measurement site surrounded by the light shielding section. measuring device. A physiological measurement device comprising:
one or more emitters configured to emit light;
a diffuser configured to be positioned between the one or more emitters and a tissue measurement site when the physiological measurement device is in use ;
a circular light shielding part;
A plurality of detectors configured to detect at least a portion of light after passing through a portion of the tissue measurement site partitioned by the light shield, wherein the tissue measurement partitioned by the light shield. a plurality of detectors arranged in an array having a spatial configuration corresponding to the shape of a portion of the site and further configured to output at least one signal in response to detected light;
A physiological measurement device comprising:
The circular light block forms a light isolation chamber that separates the plurality of detectors from the one or more emitters during use of the physiological measurement device such that the one or more emitters emit light. configured to block at least some of the emitted light from reaching the plurality of detectors without first reaching tissue;
The physiological measurement device is a processor that receives and processes one or more signals responsive to the output at least one signal, and measures a user's physiological parameter responsive to the one or more signals. A physiological measurement device, further comprising a processor configured to determine. the one or more emitters configured to emit light in an initial light pattern;
The diffuser redirects at least a portion of the light emitted from the one or more emitters such that the emitted light is directed toward a surface of the tissue measurement site, and the initial light pattern is 23. The physiological measurement device of claim 22, comprising a light transmissive material configured to produce different output light patterns. 23. A physiological measuring device according to claim 22, characterized in that said physiological parameter is oxygen saturation. 23. A physiological measuring device according to claim 22, characterized in that said physiological parameter is pulse rate.

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